EP1341480A2 - Greffon tubulaire tisse a zones de souplesse variables - Google Patents

Greffon tubulaire tisse a zones de souplesse variables

Info

Publication number
EP1341480A2
EP1341480A2 EP01991020A EP01991020A EP1341480A2 EP 1341480 A2 EP1341480 A2 EP 1341480A2 EP 01991020 A EP01991020 A EP 01991020A EP 01991020 A EP01991020 A EP 01991020A EP 1341480 A2 EP1341480 A2 EP 1341480A2
Authority
EP
European Patent Office
Prior art keywords
tube
yarns
fill
region
warp
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP01991020A
Other languages
German (de)
English (en)
Inventor
E. Skott Greenhalgh
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Secant Group LLC
Original Assignee
Prodesco Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Prodesco Inc filed Critical Prodesco Inc
Publication of EP1341480A2 publication Critical patent/EP1341480A2/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06—Blood vessels
    • A61F2/07—Stent-grafts
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06—Blood vessels
    • D—TEXTILES; PAPER
    • D03—WEAVING
    • D03D—WOVEN FABRICS; METHODS OF WEAVING; LOOMS
    • D03D15/00—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used
    • D03D15/50—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used characterised by the properties of the yarns or threads
    • D03D15/56—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used characterised by the properties of the yarns or threads elastic
    • D—TEXTILES; PAPER
    • D03—WEAVING
    • D03D—WOVEN FABRICS; METHODS OF WEAVING; LOOMS
    • D03D3/00—Woven fabrics characterised by their shape
    • D03D3/02—Tubular fabrics
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06—Blood vessels
    • A61F2002/065—Y-shaped blood vessels
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2230/0063—Three-dimensional shapes
    • A61F2230/0073—Quadric-shaped
    • A61F2230/0078—Quadric-shaped hyperboloidal
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
    • A61F2250/0015—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in density or specific weight

Definitions

  • This invention relates to woven tubular grafts having selected regions of varying flexibility and particularly to Woven bifurcated tubes for use as endoluminal grafts in the treatment of vascular aneurysms.
  • a vascular aneurysm is a pathologic dilation of a segment of a blood vessel which constitutes a weakened portion of the vessel.
  • Figure 1 shows an example of a fusiform aneurysm 10, such as can occur in the abdominal aorta 12. The entire circumference of the aorta 12 is dilated and weakened. The majority of these aortic aneurysms are located in the distal abdominal aorta between the renal arteries 14 and the bifurcation point 16 where the abdominal aorta splits into the common iliac arteries 18.
  • An aneurysm in any vascular vessel is a cause of concern, and aortic aneurysms in particular constitute a serious condition, as an acute rupture of the aneurysm is fatal unless an emergency operation is performed. However, even when such operations are performed in time, the mortality rate is still greater than 50%.
  • a stent graft 20 comprises a bifurcated fabric tube 22.
  • Bifurcated fabric tubes are formed of a plurality of interlaced yarns wherein a single tube branches into two or more tubes at a bifurcation point.
  • the term "yarn” as used herein is a generic term for a continuous strand or strands of fibers, filaments or material in a form suitable for knitting, weaving, braiding or otherwise intertwining or interlacing to from a fabric.
  • Various forms of yarn include monofilaments, filaments twisted together, filaments laid together without twist, as well as other configurations.
  • Tube 22 may be woven, knitted or braided and has one end 24 which is attached to the inner surface of the artery upstream of the aneurysm 10.
  • the opposite end 26 of the bifurcated tube is split at a septum 28 into two branch tubes 26a and 26b.
  • the branch tubes are attached to the inside surfaces of the iliac arteries 18 below the aneurysm 10.
  • the stent graft 20 is substantially impermeable to blood and replaces the abdominal aorta in the region of the aneurysm 10, relieving the pressure on the weakened arterial wall and avoiding a potentially fatal rupture.
  • woven tubes are preferred because the graft should have as little bulk as possible so that it may be readily collapsible to fit within the lumen of the catheter.
  • the graft must also be substantially impermeable in the region of the aneurysm so as to isolate and relieve the pressure on it.
  • Woven structures inherently have relatively minimal bulk when compared to knitted or braided structures having the same dimensions and can readily form a substantially impermeable membrane with low porosity. Because bifurcated grafts, with their multiple tubes, tend to be bulkier than grafts comprising a single tube, the woven structure which minimizes the bulk is especially advantageous.
  • Blood vessels are seldom round in cross-section; they tend to be oval, egg-shaped or have irregular shapes due to calcified deposits formed on the inner walls.
  • the woven bifurcated tube must sealingly join the vessel at both its ends, but the lack of radial flexibility inhibits the ability of the tube to adapt to the non-round cross section of the vessel. As shown in Figure 2 , this may result in folds 30 in either or both the vessel 12 and the tube 22 where they are joined at upstream end. The folds can result in leakage of blood past the graft at its upstream end and into the aneurysm, placing pressure on the aneurysm and possibly causing it to burst.
  • Blood vessels are seldom straight; they tend to curve in complex ways. This is readily apparent in bifurcated vessels such as the abdominal aorta 12 which in which branches 26a and 26b curve away into the iliac arteries 18 supplying blood to the lower extremities.
  • the lack of longitudinal flexibility inhibits the woven graft from readily bending to follow the curvature of the iliac arteries as they branch away from the aorta.
  • the branch 26a of the woven tube 22 may tend to buckle and bunch up on the inside part of the curve, causing folds 32 which can occlude the lumen of the graft, restricting blood flow.
  • the part of the branch 26a on the outside of the curve does not stretch to accommodate the longer path of the artery wall and tends to tug on the artery, perhaps causing a kink 34 in its wall.
  • Blood vessels tend to vary in diameter from person to person depending on the physical characteristics of the individual. Due to their inherent lack of radial flexibility, woven tubes of one particular diameter cannot readily adapt to the range of artery sizes among different people. As shown in Figure 4, if the tube 22 is too small in diameter, it may cause folds 36 in the artery 12, reducing the blood flow and causing leaks past the joint. If the tube is too large, it may tend to form an inward fold 38 and leak, as seen in Figure 5. Therefore, many sizes of grafts must be available so that the appropriate size may be matched to a particular artery size so that a good seal can be obtained between graft and artery.
  • the woven tube 22 generally does not have sufficient radial flexibility to accommodate the expansion of the vessel 12 and may result in a separation 40 of a portion of the graft from the wall of the vessel as seen in Figure 6. This may allow leakage into the aneurysm, and in extreme cases the upstream portion of the tube may fold into the lumen, inhibiting the flow of blood through the vessel.
  • Woven tubes with little radial or axial elasticity tend to be stiff. This stiffness directly affects the force required to move the stent graft through the lumen of a catheter for positioning the graft within the artery at the aneurysm.
  • the catheter is seldom straight as it must follow the bends and twists of the vessel through which it snakes, and the stiffer the graft is, the more force is required to move it through a twisting catheter lumen.
  • an endoluminal graft which has minimal bulk so that it will fit within the lumen of a catheter, is substantially impermeable and strong enough to withstand repeated hydraulic pressure cycles caused by hundreds of thousands of heart beats and yet possesses the radial and longitudinal flexibility, allowing it to move with minimal force through a curving catheter and to sealingly accommodate arteries of various shapes, sizes and curvatures without folding or kinking in order to form and maintain a fluid-tight seal between the graft and the artery in the treatment of aneurysms.
  • the invention concerns a graft compatible with living tissue, the graft comprising an elongated tube woven from a plurality of warp yarns oriented in a warp direction substantially lengthwise along the tube and a plurality of fill yarns oriented in a fill direction substantially circumferentially around the tube.
  • the warp and the fill yarns are elastic, and the tube comprises a region of relatively greater flexibility oriented in one of the warp and the fill directions.
  • the region of relatively greater flexibility is formable in the warp direction by weaving the warp yarns comprising the region under relatively less tension than the tension at which the warp yarns comprising the remainder of the tube are woven.
  • the region of relatively greater flexibility is formable in the fill direction by weaving the fill yarns comprising the region under relatively less tension than the tension at which the fill yarns comprising the remainder of the tube are woven.
  • Such a tube may also comprise a second region of relatively greater flexibility oriented again in the fill direction and located at an opposite end of the tube, the second region of relatively greater flexibility also being formed by weaving the plurality of the fill yarns comprising the second region under relatively less tension than the tension at which the fill yarns comprising the portion of the tube between the first and second regions are woven.
  • the third region of relatively greater flexibility is formed by weaving the plurality of warp yarns comprising the third region under relatively less tension than the tension at which the warp yarns comprising the first and second regions of relatively greater flexibility are woven.
  • the region of relatively greater flexibility may also be formed in the warp direction by including in the region relatively fewer of the warp yarns per unit area than the number of the warp yarns per unit area comprising the remainder of the tube.
  • the region of relatively greater flexibility may also be formed in the fill direction by including in the region relatively fewer of the fill yarns per unit area than the number of the fill yarns per unit area comprising the remainder of the tube.
  • the invention also includes a method of making a graft comprising an elongated tube compatible with living tissue and having a region of relatively greater flexibility.
  • the method according to the invention comprises the steps of:
  • a plurality of fill yarns may be woven at the third tension over a portion of the tube positioned at one end, thereby forming the region of relatively greater flexibility at the one end, the increased flexibility being in the fill direction.
  • the plurality of fill yarns may also be woven at the third tension over a second portion of the tube positioned at an opposite end thereof, thereby forming a second of the regions of relatively greater flexibility at the opposite end of the tube, the increased flexibility also being in the fill direction at the opposite end.
  • Figure 1 is a partial sectional view of a graft according to the prior art
  • Figure 2 is a partial perspective view of a graft according to the prior art
  • Figure 3 is a partial sectional view of a graft according to the prior art
  • Figure 4 is a cross-sectional view of a graft according to the prior art
  • Figure 5 is a cross-sectional view of a graft according to the prior art
  • Figure 6 is a cross-sectional view of a graft according to the prior art
  • Figure 7 is a graft comprising a woven tube according to the invention.
  • Figure 8 is a graft comprising a bifurcated woven tube according to the invention.
  • FIG. 7 shows an endoluminal stent graft 50 used to treat a fusiform aneurysm 52 in an artery 54.
  • Stent graft 50 comprises a tube 56 woven from a plurality of warp yarns 57 and fill yarns 59 and having three regions, 58, 60 and 62, of differing flexibility.
  • Regions 58 and 62 form the upstream and downstream ends, respectively, of the tube 56, where the tube attaches circumferentially around the artery 54 and must form a seal which will prevent leaks into the aneurysm 52.
  • arteries are not usually round, may have calcified occlusions, are different in size from one another and may tend to expand in diameter with age.
  • the increased radial flexibility also enhances the compliance of the tube, ensuring that the seal between tube and artery is maintained over time as the artery increases in diameter.
  • Radial flexibility of the regions 58 and 62 is controlled by using elastic fill yarns 59 in the fill direction circumferentially around the tube and varying the tension and density at which these fill yarns are woven.
  • the fill yarns are woven under relatively less tension and/or at relatively lower density (picks per length of tube) than other regions of the tube. Because they are woven under less tension, the elastic yarns are locked into the fabric substantially unstretched and are subsequently able to stretch elastically in the fill direction when required to allow radial expansion of the tube to match the diameter and shape of the artery.
  • the lower density of the fill yarns also increases the radial flexibility as there are generally fewer yarns per unit area which must be stretched, allowing the regions 58 and 62 to be expanded by relatively lower loads than if a higher density of yarns were used.
  • a side benefit of the lower weave density at the end regions 58 and 62 is that it may provide interstices of a size which encourage the ingrowth of endothelial cells which line the artery, thereby effecting a natural seal between graft and vessel.
  • the tube 56 It is not desirable that the tube 56 have significant radial flexibility in the region 60 adjacent to aneurysm 52. This region must maintain its diameter under the hydraulic pressure of the blood as it is pumped through the artery so that it relieves the pressure on the aneurysm 52. Significant radial flexibility in this region would defeat the purpose of the graft as it would allow the tube 56 to expand and place pressure on the artery at the aneurysm.
  • the radially stiff region 60 is formed by weaving the elastic fill yarns comprising the tube under relatively higher tension than the fill yarns in regions 58 and 62.
  • the tension is above the elastic limit but below the ultimate tensile strength of the fill yarns in region 60.
  • the yarns, stretched by the tension force during weaving and locked in the fabric in the stretched state, are not capable of further significant stretching elastically when radial forces are applied to the interior of the tube, as occurs, for example, due to the hydraulic pressure during heartbeats.
  • the density of the fill yarns may also be increased to provide further radial stiffness to the tube in region 60. With more yarns per unit length, it requires greater force to radially expand the tube, yielding relatively greater stiffness in the fill direction for the region 60. Greater yarn density also has the added benefit of reducing the porosity and preventing leakage of blood from the stent graft at the aneurysm.
  • the tension of the fill yarns 59 is controlled by the loom's shuttle trigger tension, which can be set to a relatively low value when region 58 is being woven, resulting in substantially unstretched fill yarns and a tube having relatively greater radial flexibility and compliance over region 58.
  • the shuttle trigger tension may be increased as region 60 is being woven to insert substantially stretched yarns in the fill direction, yielding a relatively stiff tube radially over. region 60.
  • region 62 is woven, the shuttle trigger tension is again reduced, inserting substantially unstretched fill yarns under low tension and producing a region of the tube having relatively greater radial flexibility and compliance.
  • the density of the fill yarns may be controlled by a pick wheel as is well understood in the art.
  • the elastic yarns used to weave tube 56 are preferably highly textured yarns of polyester. Polytetrafluoroethylene, polypropylene or other biocompatible materials are also feasible. The textured nature of the yarns provides the required elastic properties. Alternatively, the elastic property of the yarns may be obtained by using inherently elastic materials, such as silicone, polyurethane or rubber to form the yarns. Crimped yarns may also be employed to provide fill yarns wherein the tension may be varied to change the radial stiffness of the tube.
  • a practical example of a stent graft 50 may comprise a tube
  • region 58 12 inches in length, 1.2 inches in diameter, having fill yarns of textured polyester of 40 denier initially woven at a shuttle trigger tension of 100 grams and a fill density of 60 picks per inch to form region 58.
  • the shuttle trigger tension is then increased to 140 grams and the fill density of the fill yarns is increased to 68 picks per inch to weave region 60, being relatively stiffer in the fill direction.
  • Region 62 is then woven at the same parameters as region 58, although the parameters need not be the same.
  • FIG 8 shows a stent graft 66 used to treat a fusiform aneurysm 68 in an aortic artery 70 near the iliac arteries 72 and 74.
  • Stent graft 66 comprises a bifurcated tube 76 having a main tube 78 and two branch tubes 80 and 82. Both the main and branch tubes are woven from a plurality of warp yarns 57 and fill yarns 59, the warp yarns being oriented in a warp direction oriented lengthwise along the main and branch tubes, the fill yarns being oriented in a fill direction circumferentially around the tubes.
  • Bifurcated tube 76 provides an example of a stent graft which will benefit from controlling the flexibility of the tube in both the fill and warp directions. As described above for the tube 56, it is advantageous to provide relatively greater flexibility oriented in the fill direction (circumferentially) in regions of tube 76 such as 88, 90 and 92 which are areas where the tube requires greater radial compliance and flexibility to effect a seal to the artery. As noted above, relatively low radial flexibility is desired for the region 94 adjacent to the aneurysm. The radial flexibility characteristics for the bifurcated tube 76 are controlled in the same way as described above for the conventional tube 56, i.e., by controlling the tension under which the fill yarns are woven when forming the various regions of the tube.
  • the relative flexibility of the branch tubes 80 and 82 in the warp direction over regions 96 and 98 is controlled by using elastic warp yarns in the warp direction and weaving the warp yarns under relatively greater or lesser tension. If relatively greater flexibility in the warp direction is desired, the warp yarns are woven under relatively less tension than other regions of the tube 76. The warp yarns woven under the lower tension are substantially unstretched when they are woven into the fabric and will, therefore, be able to stretch elastically under load, allowing the tube to stretch lengthwise and accommodate the curvature of the artery. Conversely, if relatively less flexibility is desired in the warp direction, the warp yarns are stretched under relatively greater tension (preferably in excess of the elastic limit) as they are woven into the fabric.
  • the stretched yarns are locked into the fabric by the fill yarns and provide relatively little lengthwise flexibility since they are already stretched above their elastic limit and have little or no elasticity left.
  • the warp yarns are preferably highly textured yarns comprised of polyester, polytetrafluoroeth lene, polypropylene or other biocompatible materials.
  • Further control of the longitudinal flexibility may be provided by weaving the tube 76 with the warp yarns closer or farther apart, thereby controlling the warp yarn density (the number of yarns per unit length) .
  • Denser weaves are necessarily woven under relatively higher yarn tension which tends to pre- stretch the yarn, leaving little capacity for the yarn to stretch further once woven into the tube. This results in a tube with relatively less flexibility in the warp direction but achieves relatively low fabric porosity due to the relatively higher yarn density.
  • less dense weaves are woven under relatively less tension, and the warp yarns are not pre-stretched to the same degree and, when interwoven to form the tube, consequently allow it to stretch with relatively greater longitudinal flexibility.
  • Such tubes have relatively higher porosity, however, and are, therefore, more permeable. Control of the warp yarn density may be effected by varying the separation of the tines of the comb through which the warp yarns pass on the loom.
  • a practical example of a bifurcated tube 76 useable as a stent graft may comprise a main tube 5 inches in length, 1.2 inches in diameter and branch tubes 6 inches in length and 0.7 inches in diameter, the tubes being formed of textured polyester yarns of 40 denier. Fill yarns 59 in regions 88, 90 and 92 near the ends of the tubes are woven at a shuttle trigger tension of 100 grams and a fill density of 60 picks per inch to provide relatively greater flexibility in the fill direction, allowing the tube to expand radially and accommodate and seal to the vessel 70.
  • the fill yarns in region 94 located adjacent to the aneurysm 68, are woven at an increased shuttle trigger tension of 140 grams, and the fill density may be increased to 68 picks per inch to provide relatively less flexibility in the fill direction over region 94.
  • Regions 88 and 94 are woven with warp yarns under a relatively high tension of 10 grams to provide relatively lower warp direction flexibility over these regions.
  • the warp yarn tension and density is changed when branch tubes 80 and 82 are being woven. To provide relatively greater warp direction flexibility, thereby allowing the branch tubes to better follow the curve of the iliac arteries 72 and 74, the warp yarn tension is reduced to 7 grams and the warp yarn density is reduced from 140 to 130 ends per inch.
  • Fabric tubes with regions of varying flexibility in the warp and fill directions will provide improved stent grafts for the repair of vascular aneurysms.
  • Relatively greater flexibility in the fill direction will provide for a better seal between the graft and the artery, lessening the likelihood of leakage or obstruction of the artery and allow one size of graft to accommodate a wide range of different size and shape arteries.
  • Relatively greater flexibility in the warp direction will allow the graft to conform to the curvature of the artery as it twists and bends without folding or causing kinking of the vessel.
  • the overall increased flexibility is attained without significantly increasing the bulk of the graft thus allowing the graft to be more easily moved through a catheter for delivery to the site of the aneurysm.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Pulmonology (AREA)
  • Cardiology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Textile Engineering (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Gastroenterology & Hepatology (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Prostheses (AREA)
  • Looms (AREA)
  • Woven Fabrics (AREA)

Abstract

La présente invention concerne un tube tissé chaîne en long à trame circulaire. Ce tube est fait d'une pluralité de fils de chaîne élastiques parallèles venant dans le sens de la chaîne et d'une pluralité de fils de trame élastiques venant dans le sens de la trame. Dans sa longueur, le tube comporte au moins une zone isolée d'une souplesse relativement supérieure dans le sens de chaîne ou de trame. Pour obtenir cette souplesse supplémentaire, on choisit de moins tendre le fil de chaîne ou de trame selon le cas pour le tisser.
EP01991020A 2000-10-30 2001-10-30 Greffon tubulaire tisse a zones de souplesse variables Withdrawn EP1341480A2 (fr)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
US24424000P 2000-10-30 2000-10-30
US244240P 2000-10-30
PCT/US2001/047941 WO2002035989A2 (fr) 2000-10-30 2001-10-30 Greffon tubulaire tisse a zones de souplesses variables

Publications (1)

Publication Number Publication Date
EP1341480A2 true EP1341480A2 (fr) 2003-09-10

Family

ID=22921951

Family Applications (1)

Application Number Title Priority Date Filing Date
EP01991020A Withdrawn EP1341480A2 (fr) 2000-10-30 2001-10-30 Greffon tubulaire tisse a zones de souplesse variables

Country Status (4)

Country Link
US (1) US6814754B2 (fr)
EP (1) EP1341480A2 (fr)
AU (1) AU2002230774A1 (fr)
WO (1) WO2002035989A2 (fr)

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EP1414369A2 (fr) * 2001-07-27 2004-05-06 Medtronic, Inc. Prothese vasculaire poreuse renforcee par un tissu adventice
US7147661B2 (en) 2001-12-20 2006-12-12 Boston Scientific Santa Rosa Corp. Radially expandable stent
ITMO20020349A1 (it) * 2002-12-06 2004-06-07 G A M A H S Srl Protesi per grandi vasi sanguigni.
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US6814754B2 (en) 2004-11-09
US20020058992A1 (en) 2002-05-16
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AU2002230774A1 (en) 2002-05-15
WO2002035989A3 (fr) 2002-10-10

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